Evaluation of an implanted prosthesis

ABSTRACT

Evaluating an implanted hearing prosthesis, including operating the implanted hearing prosthesis, capturing sound generated by a transducer of the prosthesis during said operation, and comparing the captured sound to a sound model.

BACKGROUND

Field of the Invention

Embodiments of the present technology relate generally to prosthesessuch as active hearing prostheses, and more particularly, to theevaluation of an implanted prosthesis.

Related Art

Hearing loss is generally of two types, conductive and sensorineural.Sensorineural hearing loss is due to the absence or destruction of thecochlear hair cells which transduce sound into nerve impulses. Varioushearing prostheses have been developed to provide individuals sufferingfrom sensorineural hearing loss with the ability to perceive sound. Forexample, cochlear implants have an electrode assembly which is implantedin the cochlea. In operation, electrical stimuli are delivered to theauditory nerve via the electrode assembly, thereby bypassing theinoperative hair cells to cause a hearing percept.

Conductive hearing loss occurs when the natural mechanical pathways thatprovide sound in the form of mechanical energy to a cochlea are impeded,for example, by damage to the ossicular chain or ear canal. For avariety of reasons, such individuals are typically not candidates for acochlear implant. Rather, individuals suffering from conductive hearingloss sometimes receive an acoustic hearing aid, and sometimes seeksurgical options. Hearing aids rely on principles of air conduction totransmit acoustic signals to the cochlea. In particular, hearing aidsamplify received sound and transmit the amplified sound into the earcanal. This amplified sound reaches the cochlea in the form ofmechanical energy, causing motion of the perilymph and stimulation ofthe auditory nerve.

SUMMARY

Some aspects of the present technology are generally directed to anearplug, comprising an occluding apparatus configured to occlude an earcanal of a recipient, and a sound capture apparatus integrated with theoccluding apparatus and having a sound receiver that faces the middleear when the earplug is effectively positioned in the ear canal.

Some other aspects of the present technology are generally directed to asystem for evaluating an implanted prosthesis having a vibratingdiaphragm when in operation, comprising a sound capture apparatusconfigured to capture sound caused by the vibrating diaphragm travelingthrough a middle ear of a recipient, and to generate an audio signalrepresentative of the captured sound, and a sound analyzer configured tocompare the audio signal to a sound model.

Some other aspects of the present technology are generally directed to amethod of evaluating an implanted prosthesis, comprising, operating theimplanted prosthesis, capturing vibrations generated by a transducer ofthe prosthesis during said operation, and comparing the capturedvibrations to a vibration model.

BRIEF DESCRIPTION OF THE DRAWINGS

Embodiments of the present technology are described below with referenceto the attached drawings, in which:

FIG. 1 is perspective view of a human ear;

FIG. 2A is a perspective view of an exemplary Direct Acoustic CochlearImplant (DACI), implanted in accordance with an embodiment;

FIG. 2B is a perspective view of an exemplary Direct Acoustic CochlearImplant (DACI), implanted in accordance with an embodiment;

FIG. 2C is a perspective view of an exemplary middle ear implantimplanted in accordance with an embodiment;

FIG. 3 is a schematic depicting an exemplary implantable component inaccordance with an embodiment;

FIG. 4 is a flowchart for an exemplary method in accordance with anembodiment;

FIG. 5A depicts an exemplary earplug in accordance with an embodiment;

FIG. 5B depicts utilization of the earplug of FIG. 5A;

FIG. 6 is a flowchart for another exemplary method in accordance with anembodiment;

FIG. 7 is a flowchart for another exemplary method in accordance with anembodiment;

FIG. 8 is a flowchart for another exemplary method in accordance with anembodiment;

FIG. 9 depicts signal to noise ratio data in accordance with anembodiment;

FIG. 10A is an exemplary system in accordance with an embodiment;

FIG. 10B is an exemplary external component of a hearing prosthesis inaccordance with an exemplary embodiment;

FIG. 10C is a flowchart for another exemplary method in accordance withan embodiment;

FIG. 10D is another embodiment of an external component of a hearingprosthesis in accordance with an exemplary embodiment; and

FIG. 11 depicts an exemplary acceptance band in accordance with anembodiment.

DETAILED DESCRIPTION

FIG. 1 is perspective view of a human skull showing the anatomy of thehuman ear. As shown in FIG. 1, the human ear comprises an outer ear 101,a middle ear 105 and an inner ear 107. In a fully functional ear, outerear 101 comprises an auricle 110 and an ear canal 102. An acousticpressure or sound wave 103 is collected by auricle 110 and channeledinto and through ear canal 102. Disposed across the distal end of earcanal 102 is a tympanic membrane 104 which vibrates in response to soundwave 103. This vibration is coupled to oval window 112, which isadjacent to round window 121 through three bones of middle ear 105,collectively referred to as the ossicles 106 and comprising the malleus108, the incus 109 and the stapes 111. Bones 108, 109 and 111 of middleear 105 serve to filter and amplify sound wave 103, causing oval window112 to articulate, or vibrate in response to the vibration of tympanicmembrane 104. This vibration sets up waves of fluid motion of theperilymph within cochlea 140. Such fluid motion, in turn, activates haircells (not shown) inside cochlea 140. Activation of the hair cellscauses nerve impulses to be generated and transferred through the spiralganglion cells (not shown) and auditory nerve 114 to the brain (also notshown) where they cause a hearing percept.

FIG. 2A is a perspective view of an exemplary direct acoustic cochlearstimulator 200A in accordance with some exemplary embodiments. Directacoustic cochlear stimulator 200A comprises an external component 242that is directly or indirectly attached to the body of the recipient,and an internal component 244A that is temporarily or permanentlyimplanted in the recipient. External component 242 typically comprisestwo or more sound input elements, such as microphones 224, for detectingsound, a sound processing unit 226, a power source (not shown), and anexternal transmitter unit 225. External transmitter unit 225 comprisesan external coil (not shown). Sound processing unit 226 processes theoutput of microphones 224 and generates encoded data signals which areprovided to external transmitter unit 225. For ease of illustration,sound processing unit 226 is shown detached from the recipient.

Internal component 244A comprises an internal receiver unit 232, astimulator unit 220, and a stimulation arrangement 250A in electricalcommunication with stimulator unit 220 via cable 218 extending throughartificial passageway 219 in mastoid bone 221. Internal receiver unit232 and stimulator unit 220 are hermetically sealed within abiocompatible housing, and are sometimes collectively referred to as astimulator/receiver unit.

Internal receiver unit 232 comprises an internal coil (not shown), amagnet (also not shown) fixed relative to the internal coil. Theexternal coil transmits electrical signals (i.e., power and stimulationdata) to the internal coil via a radio frequency (RF) link. The internalcoil is typically a wire antenna coil comprised of multiple turns ofelectrically insulated platinum or gold wire. The electrical insulationof the internal coil is provided by a flexible silicone molding (notshown). In use, implantable receiver unit 232 is positioned in a recessof the temporal bone adjacent auricle 110. It is noted that otherembodiments may include a system in which some and/or all of thefunctionality of the external component 242 is included in the internalreceiver unit 232 or other implanted component (e.g., microphones areimplanted in the recipient). Such an exemplary alternate embodiment canbe in the form of a so-called implantable hearing prosthesis. In such anembodiment, the external component 242 may not be present and/or mayhave different functionality.

In the illustrative embodiment of FIG. 2A, ossicles 106 have beenremoved. However, it should be appreciated that stimulation arrangement250A can be implanted without disturbing ossicles 106, at leastdepending on the particular anatomy of a recipient.

Stimulation arrangement 250A comprises a transducer 240, a coupling rod251A, and a coupling prosthesis 252A, which in this embodiment, couplingrod 251A includes an artificial incus 261A. The coupling rod 251A isconnected to the coupling prosthesis 252A, although sometimes a definedcoupling prosthesis is not present. Transducer 240 is fixed to mastoidbone 221 via a fixation system (not explicitly shown in the FIGs.).

In this embodiment, stimulation arrangement 250A is implanted and/orconfigured such that at least a portion of coupling rod 251A is locatedin the middle ear cavity and a portion of coupling prosthesis 252A (orother coupling, if present) abuts an opening in the vestibule 129.

As noted above, a sound signal is received by microphone(s) 224,processed by sound processing unit 226, and transmitted as encoded datasignals to internal receiver 232. Based on these received signals,stimulator unit 220 generates drive signals which cause actuation oftransducer 240. The mechanical motion of transducer 240 is transferredto coupling element 252A such that a wave of fluid motion is generatedin vestibule 129. The wave of fluid motion continues into cochlea 140,thereby activating the hair cells of the organ of Corti. Activation ofthe hair cells causes appropriate nerve impulses to be generated andtransferred through the spiral ganglion cells (not shown) and auditorynerve 114 to cause a hearing percept in the brain.

FIG. 2B is a perspective view of another type of direct acousticcochlear stimulator 200B in accordance with some exemplary embodiments.Direct acoustic cochlear stimulator 200B comprises external component242 and an internal component 244B.

Stimulation arrangement 250B comprises transducer 240, optionally, acoupling element 252B (such as a stapes prosthesis) and a coupling rod251B which includes artificial incus 261B which couples the transducerto the coupling element 252B. In this embodiment, stimulationarrangement 250B is implanted and/or configured such that at least aportion of coupling rod 251B is located in the middle ear cavity and aportion of coupling element 252B abuts and/or penetrates round window121 or oval window 112 of cochlea 140. The mechanical motion oftransducer 240 is transferred to coupling element 252B such that a waveof fluid motion is generated in the vestibulum 129. The fluid motioncontinues into cochlea 140, thereby activating the hair cells of theorgan of Corti.

The embodiments of FIGS. 2A and 2B are exemplary embodiments of a DirectAcoustic Cochlear Implant (DACI) that provide mechanical stimulationdirectly to cochlea 140. Direct Acoustic Cochlear Implants (DACIs)directly provide mechanical stimulation to cochlea 140, for example viaoval window 112 or round window 121 or any other opening in vestibule129. FIG. 2C depicts an exemplary embodiment of a middle ear implant200C having a stimulation arrangement 250C comprising transducer 240 anda coupling rod 251C. Middle ear implants provide mechanical stimulationto ossicles 106 in middle ear 105. For example, middle ear implants canprovide mechanical stimulation to one of ossicles 106, such to incus 109or stapes 111. Coupling rod 251C includes a coupling prosthesis 252C andan artificial incus 261C which couples the transducer to the couplingprosthesis 252C. In this embodiment, prosthesis 252C couples to stapes111.

FIG. 3 is a perspective view of an exemplary internal component 344 ofan implant which generally represents internal components 244 describedabove. Internal component 344 comprises an internal receiver unit 332, astimulator unit 320, and a stimulation arrangement 350. As shown,receiver unit 332 comprises an internal coil (not shown), and a magnet320, which, in some embodiments, can be fixed relative to the internalcoil. Internal receiver unit 332 and stimulator unit 320 are typicallyhermetically sealed within a biocompatible housing. This housing hasbeen omitted from FIG. 3 for ease of illustration.

Stimulator unit 320 is connected to stimulation arrangement 350 via acable 328. Stimulation arrangement 350 comprises a transducer 340 with acoupling rod 353. A distal end 360 of coupling element 354 is configuredto be positioned in one or more of the configurations noted above withrespect to FIGS. 2A-2C. A proximal end of coupling element 354 isconnected to transducer 340 via coupling rod 353 and the distal end ofthe prosthesis is directly coupled to the cochlea. In some embodiments,an artificial incus is attached to coupling rod 353 and coupled to thecochlea via coupling element 354. In operation, transducer 340 vibratescoupling element 354. The vibration of coupling element 354 generateswaves of fluid motion of the perilymph, thereby activating the haircells of the organ of Corti. Activation of the hair cells causesappropriate nerve impulses to be generated and transferred through thespiral ganglion cells and auditory nerve 114.

Some embodiments of methods and systems and devices for intra- andpost-operative evaluation of a hearing prosthesis, such as a DirectAcoustic Cochlear Implant (DACI) or middle ear implant according tothose detailed above and/or variations thereof, will now be described.It is noted that some embodiments of these are directed to other typesof prostheses. In an exemplary embodiment, the devices, systems and/ormethods detailed herein and/or variations thereof are applicable to anytype of prosthesis that generates noise/sound, or other types ofvibrations, providing that the teachings detailed herein and/orvariations thereof may be practiced with such prosthesis. It is furthernoted that unless otherwise noted, the phrase “hearing prosthesis” asused herein includes any prosthesis that has utilitarian value withrespect to the auditory system, such as, by way of example, a prosthesisthat has utilitarian value associated with balance and/or tinnitus.

A high-level exemplary method will now be initially detailed to providecontext for the more detailed embodiments introduced below. In thisregard, FIG. 4 represents a flowchart for an exemplary method 400according to an exemplary embodiment. Method 400 assumes that thehearing prosthesis has already been implanted into a recipient.Accordingly, in some embodiments, while not reflected in FIG. 4, method400 can entail obtaining access to a recipient in which a hearingprosthesis has been implanted, which can include obtaining access duringan operation or other surgical procedure associated with implantation ofthe hearing prosthesis. At method action 410, the implanted hearingprosthesis is operated. In an exemplary embodiment in which theimplanted hearing prosthesis is at least part of a Direct AcousticCochlear Implant (DACI) or other middle ear implant, such as by way ofexample the middle ear implant internal component 344 of FIG. 3, themiddle ear implant can be provided with a middle ear implant stimulussignal. By way of example, this can correspond to an acoustical signalin the form of sound travelling through air to a microphone of theprosthesis, a signal (e.g., inductance signal, etc.) provided to thereceiver unit 332, a signal (electrical, optical, etc.) provideddirectly to a sound processor of the Direct Acoustic Cochlear Implant(DACI) or middle ear implant, a signal (electrical, optical, etc.)provided directly to a transducer of the middle ear implant, etc. Anydevice, system and/or method that will enable the implanted hearingprosthesis to be operated in a sufficient manner to practice at leastsome of the embodiments detailed herein and/or variations thereof can beused in at least some embodiments.

With continuing reference to FIG. 4, method action 420 includescapturing sound generated by a transducer of the hearing prosthesisduring operation of the hearing prosthesis, such as, for example, thatgenerated by transducer 340. In an exemplary embodiment, the action ofcapturing the generated sound is executed via the use of an earplughaving an occluding feature and a sound capture device, where theearplug is located in the outer ear (ear canal) 102 according to anexemplary embodiment that will be detailed below.

It is noted that while the embodiments detailed herein are generallydiscussed in terms of sound/noise generation and sound/noise capture,other embodiments of the devices, systems and/or methods detailed hereinand/or variations thereof can be utilized with other types of vibrationgeneration and vibration capture. In this regard, an exemplaryembodiment corresponds to at least some of the teachings detailedherein, where the terms sound and/or noise, etc., are replaced by theterm vibration.

Having captured the sound (or other vibration(s)) generated by thetransducer, method 400 proceeds to action 430, which entails comparingthe captured sound to a sound model (details of the sound model areprovided below). While not explicitly included in method 400, as will bedetailed below, an exemplary embodiment includes a method in which,based on the comparison made at method action 430, the position of thetransducer in the recipient (e.g., the position within artificialpassageway 219) is adjusted based on the comparison.

Some embodiments of apparatuses that can be utilized to execute at leastsome of method 400 will now be described, followed by additional detailsof methods according to some embodiments.

FIG. 5A depicts an exemplary earplug 500 according to an exemplaryembodiment, which, in some embodiments, is part of a hearing prosthesisevaluation system, as will be described in greater detail below. As canbe seen, earplug 500 includes an occluding apparatus 510 configured toocclude an ear canal 102 of a recipient. Supported by the occludingapparatus is a sound capture apparatus 520 which is integrated with theoccluding apparatus 510.

The sound capture apparatus 520, which may be a microphone, includes asound receiver 522 that faces the middle ear when the earplug 500 iseffectively positioned in the ear canal (in an exemplary embodiment, thesound receiver 522 includes a vibrating diaphragm that faces the middleear), as is depicted by way of example in FIG. 5B. In this regard, FIG.5B is an excerpt of FIG. 2B above, with the earplug 500 effectivelypositioned in ear canal 102. As can be seen, the sound receiver 522 ispositioned relative to the occluding apparatus 510 such that the soundreceiver 522 faces the middle ear 105 of the recipient when the distalend 502 of the earplug faces the middle ear 105 of the recipient.

By way of example and not by way of limitation, at least someembodiments of the earplug 500 have utilitarian value in that they areconfigured to capture sound produced by an implantable hearingprosthesis, such as the transducer 240 depicted in FIG. 5B. As can beseen, sound generated by transducer 240 travels through the middle ear105 and then into the ear canal 102 where the sound is captured by thesound capture device 520 of the earplug 500. In an exemplary embodiment,where the ear drum 104 has been raised, such as is the case in FIG. 5B,the sound is directly captured by the sound capture device 520. Notethat sound that reflects off of a solid object in the middle ear priorto being captured by the sound capture device 520 falls within the scopeof “directly captured.” This as differentiated from the scenario wherethe generated sound impinges upon the intact ear drum 104, causing theear drum 104 to vibrate, resulting in pressure waves being formed on theearplug side of the ear drum, such that the sound generated by thetransducer 240 is indirectly captured by the sound capture device 520 ofthe earplug 500.

As can be seen from the figures, the earplug 500 in general, and thesound capture apparatus 520 in particular, is connected to leads 540,which can be in electrical or optical communication with the soundcapture apparatus 520, and configured to transmit corresponding signalsrepresentative of the captured sound to another component, such as byway of example, a component that is part of the hearing prosthesisevaluation system of which the earplug is also a part. It is noted thatin some embodiments, instead of leads, a sound tube/pipe or a vibrationconduction device can be used to convey captured sound or vibrationsindicative of the captured sound away from the earplug 500. Any device,system and or method that will enable communication between the earplug500 and another component, such as another component of a hearingprosthesis evaluation system detailed below, that will enable theteachings detailed herein and/or variations thereof to be practiced, canbe used in some embodiments.

As can be seen from FIG. 5B, the occluding apparatus 510 is configuredto support the sound capture apparatus 520 in the ear canal 102 suchthat when the occluding apparatus 520 is effectively positioned in theear canal 102, the sound capture apparatus 520 is spaced from the wallof ear canal 102. While other embodiments can differ, in an exemplaryembodiment, the occluding apparatus 510 is configured to support thesound capture device 520 at least approximately concentric with the earcanal 102.

Additional features of the earplug 500 according to the exemplaryembodiment of FIG. 5A-5B include the occluding apparatus 510 extendingdistally relative to a distal end 524 of the sound capture apparatus520. In this regard, as can be seen in FIG. 5A, the occluding apparatus510 has a generally mushroom shape with a hollow extension through thelongitudinal axis 504 of the earplug 500 (with regard to the mushroomshape, a hollow extension parallel and concentric with the stem andextending through the stem and the cap), and the top (cap) of themushroom shape extends distally past the distal end 524. The hollowextension is a cavity in which the sound capture apparatus 520 islocated. As will be further understood from FIG. 5A, the occludingapparatus 510 also extends proximally relative to the distal end 524 ofthe sound capture apparatus. Note further that the configurationdepicted in FIG. 5A is characterized as having a sound receiver 522located at or proximate the distal end of the occluding apparatus (whichcorresponds to the distal end 502 of the earplug). While theconfiguration of FIG. 5A is depicted such that the sound captureapparatus 520 is directly exposed to the ambient environment, in analternate embodiment, a membrane or other covering that enables sound tobe transferred from one side thereof to the other side may cover theopening of the hollow extension (e.g., at the distal end 502 of theearplug).

Sound capture apparatus 520 includes a body 521A that includes orotherwise supports sound receiver 522. Body 521A is removably attachedto body 521B, such as, by way of example, a screw thread system,although in other embodiments, the two bodies are at least generallypermanently attached to one another. At least a portion of body 521B hasutility in that it supports lead 540, which extends at least partiallytherethrough as may be seen in FIG. 5A. Such can have utility bypreventing lead 540 from kinking or otherwise being damaged duringplacement of earplug 500 into the ear canal. Sound capture apparatus 520includes shell 523 that is interposed between (i) bodies 521A and 521Band (ii) occluding apparatus 510. The bodies 521A and 521B are attachedto shell 523. Shell 523 includes a slightly recessed area 525 thatinterfaces with protrusion 527 of the occluding apparatus 510, as may beseen. In an exemplary embodiment, protrusion 527 is an elastomericmaterial that is sized and dimensioned, with respect to its fullyexpanded state, relative to the shell 523, to form an interference fitbetween the occluding apparatus 510 and the shell 523 (and thus thesound capture apparatus 520), thereby holding the sound captureapparatus 520 therein. In some embodiments, the interference fit is suchthat the sound capture apparatus 520 may be relatively easily movedforward and backward relative to the occluding apparatus 510, at leastalong the extent of the recessed area 525, to adjust the position thesound receiver 522 relative to the distal end of the occludingapparatus. Such may have utility, by way of example, in establishing amore utilitarian position of the sound receiver 522 in the scenariowhere the location of the occluding apparatus 510 cannot be adjusted/canonly be adjusted over a relatively small range of locations relative tothe ear canal (because, for example, the occlusion functionality may notbe as utilitarian as the other locations). In other embodiments, theinterference fit generally secures the sound capture apparatus 520 tothe occluding apparatus 510.

As can be seen from FIG. 5B, at least a substantial portion 512 of theouter surface 511 of the occluding apparatus 510 is tapered toward themiddle ear 106 when the earplug 500 is located in the ear canal 102.

In the exemplary embodiment depicted in FIG. 5A, the earplug isconfigured such that the functionality of (i) the capture of soundstravelling through (including originating in) the middle ear and thecapture of sounds resulting therefrom (e.g., due to vibration of anintact ear drum resulting from those sounds) and (ii) the occlusion ofthe ear canal to substantially/effectively reduce, if notsubstantially/effectively eliminate, ambient sounds (e.g., soundsoriginating from an operating room/sounds originating from outside ofthe recipient) from reaching the sound capture device can be obtainedusing a single integrated apparatus (i.e., the earplug 500). Further, inthe exemplary embodiment depicted in FIG. 5A, the earplug is configuredto achieve both of the aforementioned functionalities by inserting asingle apparatus (i.e., earplug 500) in the ear canal. In this regard,in such an exemplary embodiment, the earplug 500 is configured such thatremoval and installation force applied to the earplug 500 at one of theoccluding apparatus 510 and the sound capture device 520 that impartsmovement thereto moves the other of the occluding apparatus and thesound capture device by substantially the same amount, at least in theabsence of elastic deformation of some and/or all of the components ofthe earplug 500 and/or the ear canal 102. In some embodiments, theearplug 500 is configured such that removal and installation forceapplied to the earplug 500 at one of the occluding apparatus 510 and thesound capture device 520 that imparts movement thereto moves the otherof the occluding apparatus and the sound capture device by substantiallythe same amount, the amount being measured after substantially all(including all) elastic deformation that occurs during the movement hasbeen reversed.

In an exemplary embodiment, the earplug 500 can be sterilized prior toinsertion into the ear canal 102. Such sterilization can be done inrelatively close temporal proximity to insertion (e.g., in a temporalmanner akin to the sterilization of devices that are reused in ahospital) and/or in relatively distant temporal proximity to insertioninto (e.g., in a temporal manner akin to the sterilization of devices atthe manufacturer thereof prior to delivery to and storage at ahospital). In this regard, in some exemplary embodiments, at leastsubstantially all outer surfaces of the occluding apparatus are madeentirely out of or substantially entirely out of one or more materialsthat are sterilizable, such as, by way of example and not by way oflimitation, silicone or other similarly sterilizable materials.

Exemplary sterilization procedures for sterilizing at least the outersurfaces of the earplug 500 include gamma ray sterilization, autoclavesterilization, and Ethylene Oxide (EtO) sterilization, such that thesound capture apparatus 520 remains functional/operational for use asdetailed herein and/or variations thereof after sterilization.Accordingly, in some embodiments, at least substantially all outersurfaces and/or substantially all components of the earplug 500 are madeentirely or substantially entirely out of materials that aresterilizable by one or more or all of the aforementioned processes.

As noted above, earplug 500 can be used when executing method action 420above to capture the sound generated by a transducer of an implantedhearing prosthesis during operation of the hearing prosthesis (bothduring the implantation surgery/procedure andpost-implantation/post-operatively (e.g., during a fitting session in aclinic or at home, hours, days, weeks, months or years after theprocedure)). Thus, the earplug 500, can be used in vivo. Earplug 500 canalso be used pre-implantation. Such can be the case if a test bedmimicking the outer and middle ear of a human (with and/or withoutmimicking the presence of an intact ear drum, as some uses of theearplug 500 and the other teachings detailed herein are associated withuse on a ruptured, removed, not present, and/or flapped ear drum) isutilized, although in other embodiments, a test bed may not be utilizedproviding that sufficient sound from the transducer can be captured. Thesound captured during method action 420 can be, in some embodiments, thesound of a moving component of the transducer 340 that moves when thetransducer is stimulated. For example, such a component can be adiaphragm of the transducer that is used, for example, to hermeticallyseal the interior of the transducer 340 on the side of the transducer atwhich the coupling rod 353 is located. In an exemplary embodiment of atransducer 340, the diaphragm can be a relatively thin titanium disk,having a thickness of between about 5 to 50 micrometers. The couplingrod 353 can extend through the center of the diaphragm. Stimulation ofthe transducer results in movement of the coupling rod 353 and thusmovement of the diaphragm (e.g., vibration of the diaphragm), at leastin embodiments in which the diaphragm is mechanically linked to thecoupling rod 353. This movement of the diaphragm creates sound. It isthis sound that some embodiments of the earplug 500 can be used tocapture, although it is noted that method 400 can be practiced with adevice different from earplug 500.

FIG. 6 represents a flowchart for an exemplary method 600 according toan exemplary embodiment. Method 600 starts with method action 610, whichentails executing at least method action 430 (comparing the capturedsound to a sound model) of method 400, although in other embodiments,some additional actions or all actions of method 400 are executed.

After method action 610 is executed, method action 620 is executed (withor without additional actions there between). Method action 620 entailsquantifying performance of the transducer based on the comparison ofaction 610. In an exemplary embodiment, the quantification of theperformance of the transducer based on the comparison is accomplishedvia a transfer function. By way of example, during the surgicalimplantation of the transducer 340, the ear drum 102 may be flapped,pierced, raised, removed, etc., although in other exemplary procedures,the ear drum may already be ruptured or not be present in the firstinstance. In this regard, the captured sound propagates from thetransducer to the sound capture device through an opening in a boundaryotherwise present due at least to the tympanic membrane.

Accordingly, a direct path between the transducer 340 and the soundcapture device of the earplug 500 (or other device having the soundcapture capabilities of the earplug 500) exists, and thus soundgenerated by the transducer (or other sound generated within the cavityof the mastoid bone and/or within the middle ear) will not encounter animpassible obstacle (e.g., an obstacle that the sound cannot travelaround) at least until reaching the earplug 500. It should beappreciated that the presence of an air opening in the tympanic membraneis not utilized in some embodiments. For example, during post-operativemeasurements, the tympanic membrane will be intact in normal situations.

In an exemplary embodiment, the quantification of the performance of thetransducer based on the comparison is performed without utilizing areverse transfer function, such as, by way of example, through themeasurement of another vibrating source (e.g., tympanic membrane) thatvibrates due to the sound from the transducer striking the vibratingsource, or the measurement of vibrations generated by the anothervibrating source.

FIG. 7 represents a flowchart for an exemplary method 700 according toan exemplary embodiment. Method 700 starts with method action 710, whichentails implanting a transducer of a hearing prosthesis, such astransducer 340, in a recipient. It is noted that method action 710 canbe accomplished via a permanent or a temporary implantation of thetransducer. After executing method action 710, which may or may not bepreceded by additional actions not detailed herein, method action 720 isexecuted, which entails executing at least method action 430 (comparingthe captured sound of the transducer to a sound model) of method 400. Itis noted that method action 720 can include one or more or alladditional actions of method 400.

At method action 730, a determination is made as to whether theimplanted transducer is functioning and/or will function in autilitarian manner sufficient for an implantable hearing prosthesis,based on the comparison of the captured sound of the transducer to asound model. By way of example and not by way of limitation, thetransducer can be damaged during and/or before implantation and/or thetransducer can be improperly anchored/aligned, etc. The transducer canalso become damaged and/or dislodged after implantation. One or more orall of these scenarios can result in the transducer not functioning in autilitarian manner. Also, one or more or all of these scenarios canresult in sound produced by the transducer during stimulation beingdifferent from that which would be produced by the transducer if thetransducer was not damaged during and/or before implantation and/or thetransducer was properly anchored/aligned, etc., respectively. This soundwhich would be produced by the transducer if the transducer was notdamaged during and/or before implantation and/or the transducer wasproperly anchored/aligned, etc., corresponds to the sound of the soundmodel of action 430, as will be detailed below. Accordingly, based onthe comparison of the sound produced by the transducer to that of thesound model (e.g., the sound which would be produced by the transducerif the transducer was not damaged during and/or before implantationand/or the transducer was properly anchored/aligned, etc.), thedetermination is made as to whether the implanted transducer isfunctioning and/or will function in a utilitarian manner sufficient foran implantable hearing prosthesis.

After executing method action 730, which may or may not be preceded byadditional actions not detailed herein, based on the determination madeat method action 730, method 730 either proceeds to method action 740 ormethod action 750. If a determination is made that the implantedtransducer is functioning and/or will function in a utilitarian mannersufficient for an implantable hearing prosthesis, method action 740 isexecuted, which entails leaving the implanted transducer implanted(i.e., not removing the transducer from the recipient). If adetermination is made that the implanted transducer is not functioningand/or will not function in a utilitarian manner sufficient for animplantable hearing prosthesis, method action 750 is executed, whichentails removing the implanted transducer. Accordingly, method action750 entails removing the implant from the recipient based on thecomparison between the sound produced by the transducer and the soundmodel.

Method 700 includes an optional method action 760, which is optionallyexecuted after method action 750 is executed. Method action 760 entailsimplanting a new implant (different implant from that removed) in therecipient. Because method action 760 is executed upon a determinationthat the implanted implant is not functioning and/or will not functionin a utilitarian manner sufficient for an implantable hearingprosthesis, method action 760 entails implanting a new implantablehearing prosthesis in the recipient based on the comparison between thesound produced by the transducer and the sound model.

An exemplary method includes evaluating a signal to noise ratio relatedto the sound captured in method action 420. In this regard. FIG. 8presents method 800, which one or more or all method actions can beexecuted between method actions 420 and 430 of method 400. Method 800includes method action 810, which entails obtaining data based on asignal to noise ratio related to the captured sound. The data based onsignal to noise can comprise respective data for a plurality of signalto noise ratios for a plurality of respective frequency ranges. FIG. 9presents an example of such data divided amongst various frequencyranges. Action 820 of method 800 entails evaluating the obtained databased on the signal to noise ratios. The evaluation can result in adetermination that there is too much background noise associated withthe captured sound and thus method action 830 should be executed, whichentails capturing additional sound (e.g., method action 410 and 420should be repeated). In such an eventuality, one or more or all of themethods detailed herein and/or variations thereof can include the actionof repositioning the earplug 500 or corresponding apparatus to betterocclude the ear canal, thereby reducing the amount of ambient noise thatis captured by the sound capture apparatus of the earplug 500.Alternatively or in addition to this, the action of reducing the ambientnoise can be executed, such as, by way of example, switching offmachines in the proximity of the patients or during post-operativemeasurements, requiring healthcare professionals proximate the recipientto stop talking and/or moving while action 420 is executed.

The evaluation can result in a determination that any background noiseassociated with the captured sound is minor or relatively minimal andthus no additional sound needs to be captured (action 840 of method800).

It is noted that the evaluation of action 820 can be automated.Alternatively or in addition to this, the evaluation can be performed bythe surgeon or other healthcare professional based on the data (e.g.,the surgeon can look at a graph akin to that depicted in FIG. 9, andextrapolate a generalized conclusion about whether or not there is toomuch background noise associated with the captured sound).

It is further noted that at least some and/or all devices, systemsand/or methods detailed herein and/or variations thereof, and anycomponents thereof (e.g., individual method actions) can bepracticed/utilized before, during and after surgery and/or implantationprocedures. In some embodiments, some and/or all method actions can beexecuted while the transducer is not coupled to, for example, thecochlea or one of the ossicles, etc.

Some embodiments include devices and/or systems configured to executeone or more of all of the method actions detailed herein and/orvariations thereof. FIG. 10 presents one such example with respect tosystem 1000. System 1000 is a system for evaluating an implanted hearingprosthesis, such as the transducer 340, having a vibrating diaphragmwhen in operation. As can be seen, system 1000 includes a sound captureapparatus 1010 configured to capture sound caused by the vibratingdiaphragm that travels through a middle ear of a recipient, and togenerate an audio signal representative of the captured sound. In anexemplary embodiment, sound capture apparatus 1010 can correspond to thesound capture apparatus 520 of earplug 500, as depicted in FIG. 10.

System 1000 can further include a controller 1020 configured to activatean implanted hearing prosthesis, such as to activate transducer 340,such that the hearing prosthesis generates sounds due to the activation.Controller 1020 can correspond to the external component 242, which, asnoted above, can include a sound processor. While external component 242is depicted herein as a so-called button sound processor, in otherembodiments, external component 242 can be a so-called behind-the-ear(BTE) device to which an inductance coil has been attached. In thisregard, such controllers can utilize inductance to control the implantedhearing prosthesis in a manner akin to how the external component 242would control the prosthesis. That said, in other embodiments, thecontroller 1020 can control the prosthesis via electrical leads. Anydevice that can activate the implanted hearing prosthesis that is thesubject of use of the system 1000 so as to implement the teachingsherein and/or variations thereof can be used as the controller.

As can be seen from FIG. 10, the lead from the sound capture apparatus1010 extends from the earplug 500 to the controller 1020. In thisregard, controller 1020 both controls the prosthesis and receives inputfrom the sound capture device 1010. Accordingly, the lead(s) from soundcapture device 1010 can be fitted with an adapter so as to electricallyinterface with an input jack on controller 1030 (which can be an inputjack on, for example, a BTE, which is used to supply an audio signalfrom, for example, a portable MP3 player or the like directly to theBTE).

The system 1000 can further include a sound analyzer 1030, which is insignal communication with controller 1020, and is configured to comparethe audio signal from the sound capture device 1010 to a sound model(details of the sound model are provided below). In this regard, thesound analyzer can be a device configured to execute method action 430of method 400. Lead(s) can extend between the controller 1020 and thesound analyzer 1030. Accordingly, the lead(s) can be fitted with anadapter so as to electrically interface with an output jack oncontroller 1030 (which can be an output jack on, for example, a BTE).

In an exemplary embodiment, the system 1000 is configured to capture andanalyze sound directly produced by an implantable hearing prosthesis,although in other embodiments, the system 1000 can capture sounddirectly and indirectly.

Sound analyzer 1030 can be a computer, such as a personal computer or amainframe computer, including software and/or firmware and/or anyprogram product that enables the comparison of the audio signal from thesound capture apparatus to the sound model. While controller 1020 isdepicted as a separate component from sound analyzer 1030, in analternate exemplary embodiment, the controller 1020 and the soundanalyzer 1030 can be an integrated component.

As noted above, an exemplary method includes evaluating data based onsignal to noise ratios. Accordingly, in an exemplary embodiment, system1000 includes a signal to noise ratio analyzer 1040 that is configuredto execute at least method action 820 of method 800 as detailed above,such execution being done automatically. While signal to noise ratioanalyzer 1040 is depicted as a separate component from sound analyzer1030, in an alternate exemplary embodiment, the signal to noise ratioanalyzer 1040 and the sound analyzer 1030 can be an integrated component(e.g. both can reside on the same computer via programming).

As detailed above, controller 1020 and sound analyzer 1030 can be anintegrated component, and sound analyzer 1030 and noise ratio analyzer1040 can be an integrated component. Thus, controller 1020, soundanalyzer 1030 and noise ratio analyzer 1040 can be an integratedcomponent. Accordingly, in embodiments where the controller 1020corresponds to the external component 242 (e.g., a button soundprocessor or a BTE device, etc.), the external component 242 can havesuch functionality. Such a configuration can have utility in that it canenable a recipient of the external component 242 and a direct acousticcochlear stimulator to independently initiate an evaluation of thestimulator, as will now be detailed.

FIG. 10B depicts an exemplary embodiment of an external component 1050of a hearing prosthesis having such an integrated component embodied ina BTE device 1060 (an external component having the functionality of,for example, external component 242 detailed above) and also having thefunctionality of controller 1020, sound analyzer 1030 and noise ratioanalyzer 1040 (although in some embodiments, the functionality of thesound analyzer 1030 and/or the noise ratio analyzer 1040 may not bepresent). It is noted that in an alternate embodiment, the integratedcomponent can be embodied in a button sound processor or any otherdevice that will enable the teachings detailed herein and/or variationsthereof in general, and in particular the teachings detailed in thefollowing paragraphs. More particularly, in some embodiments, externalcomponent 1050 corresponds to system 1000 as detailed above.

As can be seen in FIG. 10B, BTE device 1060 includes a lead 1070 that isconnected to BTE device 1060. This lead leads to sound capture apparatus1010 of earplug 500 which, as detailed above, is configured to capturesound caused by the vibrating diaphragm that travels through a middleear of a recipient, and to generate an audio signal representative ofthe captured sound. It is noted that while the embodiment depicted inFIG. 10B shows lead 1070 connecting to the BTE device 1060 at the earhook location, in other embodiments, the lead may be connected atanother location. In this regard, the embodiment depicted in FIG. 10Btakes advantage of existing BTE device designs where input from amicrophone, such as a microphone from an in-the-ear (ITE) device or earhook mounted microphone is inputted into the BTE device at this location(some additional details of such designs are detailed below with respectto FIG. 10D).

It is noted that in an exemplary embodiment, a recipient of the BTEdevice 1060 utilizes it in a manner that one utilizes such a device whenpart of a hearing prosthesis, owing to the fact that it can have thefunctionality of external component 242. Namely, it is used to enhancehearing. During such use, sound is captured by a device configured tocapture ambient sound, such as through the use of an ITE device mountedmicrophone or an ear hook mounted microphone. However, the recipient candetach the microphone and attach earplug 500 to the BTE device 1060 toachieve the configuration of external component 1050 as depicted in FIG.10B, thus, when the BTE device 1060 has the functionality of at leastcontroller 1020, enabling the recipient to initiate evaluation of animplanted direct acoustic cochlear stimulator.

More particularly, FIG. 10C provides a flow chart for an exemplarymethod 1090 according to an embodiment of using external component 1050.At method action 1091, the recipient of BTE device 1060 (or a buttonsound processor having similar and/or the same functionality) and adirect acoustic cochlear stimulator utilizes the BTE device 1060 and thedirect acoustic cochlear stimulator to enhance hearing. This can occurover a period (continuously or intermittently) of days, weeks, a month,six weeks, two months or more). At some point during or after thisperiod, at method action 1092, the recipient attaches earplug 500 to theBTE device 1060 (which may require or otherwise be associated with thedisconnection of a microphone used to capture ambient sound, if the sameinput jack is to be used). The earplug 500 may be stored at therecipient's home or the like, and attached to the BTE device 1060 whenneeded, and otherwise not used when not needed. Alternatively or inaddition to this, the earplug 500 may be shipped to the recipient whenneeded (e.g., near the end or after the end of the aforementioned periodof use of the BTE device to enhance hearing, and then shipped back to alocation where it can be sterilized or the like for reuse.

At method action 1093, the earplug 500 is placed into the recipient'sear canal by the recipient. With the BTE device 1060 attached to theearplug 500, at method action 1094, the BTE device 1060 is activated toexecute at least method actions 410 and 420 of method 400, or all ofmethod 400. In this regard, operation of the implanted hearingprosthesis (action 410) occurs as a result of the BTE device 1060controlling the implanted stimulator. Such activation may be activateddirectly by the recipient, or may be activated via a link to a remotelocation (e.g., via the internet or the like). In embodiments thatexecute method action 430 of method 400, method 1090 can include theaction of providing an indication that the captured sound compares tothe sound model in a manner indicative of a properly functioningactuator if such is the case (congruence between the captured sound andthe sound model), and providing an indication that the captured soundcompares to the sound model in a manner indicative of an improperlyfunctioning actuator if such is the case (lack of congruence between thecaptured sound and the sound model). This indication may be provided tothe recipient and/or to a location remote from the recipient and theexternal component.

It is noted that in some embodiments, method 1090 may include executingmethod 600 after executing one or more of the actions of method 400.

FIG. 10D presents an alternate embodiment of an external component 1051,which has the functionality of external component 1050 detailed above.However, external component 1051 includes an ITE device 1080 connectedto the BTE device 1060 via lead 1071. ITE device 1080 includes amicrophone 1082 configured to capture ambient sound as is enabled by theart. However, ITE device 1080 is different from prior art ITE devices inthat it also includes a sound capture apparatus (not shown) on theopposite side of the ITE device 1080 from microphone 1082. That is,instead of facing outward from the ear canal, the sound captureapparatus faces inward, towards the middle ear. In an exemplaryembodiment, the sound capture apparatus of the ITE device has thefunctionality of the sound capture apparatus of earplug 500. In anexemplary embodiment, ITE device 1080 has the functionality of earplug500.

The exemplary embodiment of FIG. 10D enables execution of some or all ofmethod 400 (and some or all of method 600) via BTE device 1060 withoutattaching earplug 500 to the BTE device 1060. In an exemplaryembodiment, the sound capture apparatus is normally not activated (e.g.,such as when the microphone 1082 is used during hearing enhancement),but is activated when method 400 and/or method 600 is executed using theBTE device 1060.

As noted above, embodiments of external component 1050 (or 1051) are notlimited to the use of BTE devices. In an exemplary embodiment, element1060 can be a button sound processor. In such an exemplary embodiment,the earplug 500 (or ITE device 1080) may communicate wirelessly withbutton sound processor, although in other embodiments, communication maybe executed wirelessly. Any device system and/or method that will enablethe teachings detailed herein and/or variations thereof associated withenabling the recipient to partake in executing at least some actions ofmethod 400 and/or some actions of method 600 may be utilized in someembodiments.

The exemplary embodiments of external components 1050 and 1051 detailedabove have been described in terms of each having an analyzercorresponding to sound analyzer 1030, thus permitting method action 430to be executed. However, in other embodiments, external components areconfigured to enable the captured sound to be transmitted to a locationremote from the external component. This functionality may be asubstitute for or an addendum to the functionality associated with soundanalyzer 1030 (i.e., the sound analyzer 1030 may or may not be presentin the external components). Such may have utility in a scenario wherethe transmitted captured sound is analyzed at a remote location. Thatis, instead of being analyzed by the external component, it is analyzedby a computer or audiologist or other device, system and/or method at alocation remote from the recipient.

Some exemplary features of the sound model referenced above will now bedescribed. In an exemplary embodiment, the sound model is a model ofsound produced by an implanted transducer of an implanted hearingprosthesis, such as transducer 340. The sound model can be based on oneor more variables. Indeed, in at least some exemplary embodiments, anyvariable(s) that will enable the devices, systems and/or methodsdetailed herein, including the comparisons detailed herein, and/orvariations thereof, can be utilized.

In an exemplary embodiment, the sound model is a model based on an idealoutput from the hearing prosthesis for a given transducer stimulation.The ideal output is an output for a properly functioning and/orimplanted transducer (i.e., one that is not damaged and/or properlycoupled/aligned, etc.). The ideal output can be based on empiricaland/or computational data. Additional details associated with thedevelopment of the sound model and the variables upon which it can bebased will now be described by way of example and not by way oflimitation. In this regard, any data that will enable the development ofthe sound model can be data upon which the sound model is based.

The sound model can take into account dampening that may occur as aresult of sound traveling from the transducer through the middle earand/or through the outer ear ear canal, to the extent that the soundmust travel there through, to the sound capture apparatus. Because thesound is directly captured owing to the folding, etc., of the ear drum,such dampening can be, in some models, only about 1, 2, 3, 4, 5, 6, 7,8, 9, or 10 dB, or any range encompassing these values. Some soundmodels can disregard the dampening as such dampening can be nominal inview of other variables.

The sound model can be based on an ideal decibel level. In this regard,the sound capture device can output a signal indicative of the decibellevel of the sound captured at the sound capture apparatus (this can bebased on a voltage/amplitude varying signal, a frequency varying signal,etc., output from the sound capture apparatus), and this output can becompared to such a sound model. It is noted that the sound model basedon an ideal decibel level can be a model that utilizes voltage level ifvoltage level is indicative of an ideal decibel level. That is, by wayof example, output voltage from the sound capture device can be comparedto a voltage level indicative of an ideal decibel level withoutconverting the voltage(s) to the corresponding decibel levels.

The sound model can be based on an ideal output transfer curve. In thisregard, the sound capture device can output a signal indicative of theintensity of the sound captured at the sound capture apparatus over arange of frequencies (FIG. 9 depicts the transducer output vs. frequencyfor such output, and this output can be compared to a sound model basedon an ideal output transfer curve.

The sound model can be a parametric model. In this regard, the model maynot be a “perfect” model, but instead can be based on differentvariables that approximate a properly functioning transducer.

In an exemplary embodiment, the sound model corresponds to an“acceptance band.” In such an embodiment, comparison of the capturedsound (output from the sound capture device) to the sound model canentail determining whether the output from the sound capture devicefalls within the acceptance band. Output that falls within theacceptance band is indicative of a properly functioning/properlyanchored implanted transducer. Output that falls outside the acceptanceband is indicative of a malfunctioning/improperly anchored implantedtransducer.

FIG. 11 depicts an exemplary acceptance band 1110 for variousfrequencies. FIG. 11 also depicts output values 1120 for variousfrequency bands, and a curve 1130 fit to those output values. As can beseen, curve 1130 falls within the acceptance band 1110. Accordingly,curve 1130 is indicative of a properly functioning/properly anchoredimplanted transducer.

Curve 1130 corresponds to a transfer function of the transducer. Becauseit is based on sound captured directly from the transducer, it is adirect transfer curve of the transducer (as opposed to a reversetransfer curve). In an exemplary embodiment, the direct transfer curve,and thus the transfer function, is a mathematical representation of therelationship between input and output of a given system in terms offrequency. In an exemplary embodiment, the given system is a hearingprosthesis. A relationship exists between the input of the hearingprosthesis and an output of the hearing prosthesis. This relationship ischaracterized for a given number of different frequency bands. Byplacing the measured values for each frequency band next to each otheron a single graph in ascending order, a transfer curve is obtained.

In an exemplary embodiment, again where the observed system is thehearing prosthesis, the transfer function is a relationship that existsbetween the applied voltage (input of the hearing prosthesis) and thesound pressure level the device produces in response to that voltage(output of the hearing prosthesis), characterized for a certain amountof different frequency bands.

In an exemplary embodiment, system 1000 can be configured to deduce thetransfer function, including the direct transfer function, of theimplantable hearing prosthesis (e.g., transducer 340).

In an exemplary embodiment, the acceptance band 1110 (and thus the soundmodel), is based on variations of the output transfer function ofdifferent transducers. By way of example, such variations can be due toa varying resonance frequency of the transducer, damping associated withthe coupling to the inner ear, a fitting constant or a mean deviationbased on empirical data of the implanted transducer.

It is noted that some exemplary embodiments include adjusting the soundmodel from its original values, at least in some instances. In thisregard, as detailed above, the sound model is a model based on an idealoutput from the hearing prosthesis for a given transducer stimulation.However, the model may be refined or otherwise adjusted as a result ofthe acquisition of data or information beyond that on which the model isbased (i.e., ideal output). By way of example, such data may be deviceor patient data, and may be acquired through a fitting procedure or thelike. Using this information, an adjusted sound model unique for a givenrecipient and/or implanted transducer can be developed, and can beutilized in subsequent evaluations of that particular recipient and/ortransducer. For example, upon a determination that the transducer isfunctioning properly based on an initial comparison of captured sound tothe sound model, the sound model may be adjusted based on the capturedsound. That is, the captured sound will deviate somewhat from the soundmodel, but that deviation will be an acceptable deviation, and the soundmodel is adjusted accordingly. This adjusted sound model cansubsequently be used to determine whether the implanted transducer hasexperienced a change in performance from the time that the sound modelwas adjusted. This as contrasted to comparing captured sound at a laterdate to the sound model based on the ideal output, which might onlyreveal that the captured sound is still within acceptable deviation ofthe sound model. Such can permit the customization of a sound model to agiven recipient and/or transducer.

Alternatively and/or additionally, a scenario may exist where thecomparison of the captured sound to the sound model is indicative of atransducer functioning in a less than desirable or optimal manner, butthe recipient indicates sufficient functionality of the transducer.Instead of explanting the transducer, the captured sound may be utilizedas a new sound model, or the sound model may be modified based on thecaptured sound, and the new or modified sound model can then be used infuture evaluations and/or fitting routines.

While various embodiments have been described above, it should beunderstood that they have been presented by way of example only, and notlimitation. It will be apparent to persons skilled in the relevant artthat various changes in form and detail can be made therein withoutdeparting from the spirit and scope of the invention. Thus, the breadthand scope of the present invention should not be limited by any of theabove-described exemplary embodiments, but should be defined only inaccordance with the following claims and their equivalents.

What is claimed is:
 1. A system for evaluating an implantable prosthesishaving a vibrating component when in operation as a result of receptionby the implantable prosthesis of a stimulus signal in the form of an RFsignal that travels through skin of a recipient of the implantableprosthesis to reach the implantable prosthesis, comprising: a vibrationcapture apparatus configured to capture vibration caused by thevibrating component traveling through a middle ear of a recipient, andto generate a signal different from the RF signal that is representativeof the captured vibration; and an analyzer configured to compare thesignal to a vibration model.
 2. The system of claim 1, wherein: theprosthesis is a hearing prosthesis; the vibrating component causessound; the vibration capture apparatus is a sound capture apparatusconfigured to capture sound caused by the vibrating component travelingthrough the middle ear of a recipient; the signal is an audio signalrepresentative of the captured sound; the vibration model is a soundmodel; and the analyzer is a sound analyzer configured to compare theaudio signal to the sound model.
 3. The system of claim 2, wherein: thesound analyzer is a personal computer including a software programconfigured to compare the captured sound signal to the sound model. 4.The system of claim 2, wherein: the sound model is a model of soundproduced by an implanted transducer of the prosthesis.
 5. The system ofclaim 4, wherein: the implanted prosthesis comprises a transducer of oneof a Direct Acoustic Cochlear Implant (DACI) and middle ear implant. 6.The system of claim 2, wherein the sound model is a parametric model. 7.The system of claim 2, wherein the system is configured to capture andanalyze sound produced by an implanted prosthesis.
 8. The system ofclaim 7, wherein: the system is configured to capture and analyze sounddirectly produced by an implantable prosthesis.
 9. The system of claim2, wherein: the system is configured to deduce a direct transferfunction of an implantable prosthesis.
 10. The system of claim 2,further comprising: a controller configured to stimulate an implantedprosthesis such that the prosthesis generates sounds due to thestimulation.
 11. The system of claim 10, wherein: the implantedprosthesis is one of a Direct Acoustic Cochlear Implant (DACI) andmiddle ear implant.
 12. The system of claim 2, further comprising: asignal to noise ratio analyzer.
 13. The system of claim 2, wherein: thesound model is a model based on an ideal output transfer curve.
 14. Thesystem of claim 13, wherein: the sound analyzer is configured to comparedata based on the captured sound to a range of output levels along thefrequency curve.
 15. The system of claim 14, wherein: the range ofoutput levels are based on variations of one or more transducers due tothe varying resonance frequency, damping, pressure, temperature, afitting constant and a mean deviation from the average implant transferfunction.
 16. A method of evaluating an implanted prosthesis,comprising: operating the implanted prosthesis; capturing vibrationsgenerated by a transducer of the prosthesis during said operation;comparing the captured vibration to a vibration model, wherein thevibrations travel from the transducer, through the recipient, to avibration capture apparatus that captures the vibrations; and evaluatingthe performance of the implanted prosthesis based on the comparison,wherein the action of operating the implanted prosthesis includesproviding the implanted prosthesis with a stimulus signal in the form ofan RF signal that travels through skin of the recipient to reach theimplanted prosthesis.
 17. The method of claim 16, wherein: theprosthesis is a hearing prosthesis; the captured vibrations are capturedsound; and the vibration model is a sound model.
 18. The method of claim17, wherein: the captured sound is sound generated by a diaphragm of thetransducer.
 19. The method of claim 17, wherein: the captured sound issound generated by stimulation of the transducer of one of a DirectAcoustic Cochlear Implant (DACI) or middle ear implant.
 20. The methodof claim 17, wherein: the captured sound is sound directly propagatingfrom the transducer.
 21. The method of claim 17, further comprising:quantifying performance of the transducer based on the comparison via adirect transfer function.
 22. The method of claim 17, furthercomprising: quantifying performance of the transducer based on thecomparison without utilizing/recording a reverse transfer function. 23.The method of claim 17, further comprising: implanting the transducer inthe recipient; and adjusting the position of the transducer in therecipient based on the comparison.
 24. The method of claim 17, wherein:the captured sound propagates from the transducer to a sound capturedevice that captures the sound through an opening in a boundaryotherwise present due at least to the tympanic membrane.
 25. The methodof claim 17, further comprising: implanting the transducer in therecipient; removing the transducer from the recipient based on thecomparison; and implanting a new transducer in the recipient based onthe comparison.
 26. The method of claim 17, further comprising:obtaining data based on a signal to noise ratio related to the capturedsound; evaluating the data based on the signal to noise ratio; andcapturing additional sound generated by the transducer during asubsequent operation from the operation that generated the capturedsound based on the evaluation of the data based on the signal to noiseratio.
 27. The method of claim 26, wherein: the signal to noise ratiocomprises a plurality of signal to noise ratios for a plurality offrequency ranges.
 28. The system of claim 1, wherein: the analyzer ispart of an external component of the implantable hearing prosthesis. 29.The system of claim 28, wherein: the analyzer is part of a BTE device ora button sound processor.
 30. A hearing prosthesis, comprising: acontrol system configured to activate an implantable device having avibrating component that vibrates when in operation; a sound captureapparatus configured to capture ambient sound originating from a sourceexternal to the recipient; the vibratory component; a sound processor,wherein the hearing prosthesis is configured such that the soundprocessor processes signals outputted by the sound capture apparatus inresponse to the captured ambient sound and is configured to generate asignal provided based on the processing to be provided to the vibratorycomponent to cause the vibratory component to vibrate to evoke a hearingpercept due to the vibration of the vibratory component; and a vibrationcapture apparatus separate from the sound capture apparatus configuredto capture vibration caused by the vibrating component traveling througha recipient, and to generate a signal representative of the capturedvibration.
 31. The hearing prosthesis of claim 30, further comprising: aBTE device or a button sound processor, wherein the control system, thesound capture apparatus and the sound processor is part of the BTEdevice or the button sound processor, respectively, and the vibrationcapture apparatus is in electronic communication with BTE device or thebutton sound processor, respectively.
 32. The hearing prosthesis ofclaim 30, further comprising: an analyzer configured to compare thesignal to a vibration model.
 33. The hearing prosthesis of claim 30,wherein: the hearing prosthesis is configured to transmit the generatedsignal representative of the captured sound to a location remote fromthe hearing prosthesis.
 34. The hearing prosthesis of claim 32, wherein:the hearing prosthesis is configured to provide a recipient anindication of at least one of: congruence between the signal and thevibration model; or lack of congruence between the signal and thevibration model.
 35. The system of claim 1, wherein: the vibration modelis a model of vibration produced by the vibrating component.
 36. Thesystem of claim 35, wherein: the vibration model addresses dampeningresulting from vibrational travel from the vibrating component to thevibration capture apparatus.
 37. The system of claim 35, wherein: thevibration model is based on at least one of an ideal decibel level or anideal output transfer curve.
 38. The system of claim 1, wherein: thevibration model is a parametric model.
 39. The system of claim 1,wherein: the vibration model corresponds to an acceptance band.
 40. Themethod of claim 16, wherein: the evaluated implanted prosthesis isimplanted in a person without natural hearing.
 41. The hearingprosthesis of claim 30, wherein: the hearing prosthesis is configuredsuch that the vibration capture apparatus is removable from the hearingprosthesis, and the hearing prosthesis is configured to evoke a hearingpercept in the absence of the vibration capture apparatus.
 42. Thesystem of claim 1, wherein: the analyzer is configured to compare thesignal to the vibration module utilizing at least one of software orfirmware.
 43. The method of claim 17, wherein: the operation of theprosthesis results in components of the transducer moving relative toone another such that sound is produced by those components that isdelta to output of the prosthesis that is used to impart a hearingpercept, wherein the components moving relative to one another generatethe vibration which corresponds to the captured sound.
 44. The method ofclaim 17, wherein: the implanted prosthesis is a prosthesis configuredto output only mechanical force directly to tissue of a recipient. 45.The method of claim 17, wherein: the captured vibrations are generatedby a transducer of the prosthesis during said operation first travelsthrough the middle ear of a recipient of the implanted prosthesis andthen into the ear canal of the recipient to a device that captures thevibrations.
 46. The method of claim 17, further comprising: occluding anear canal of the recipient of the implanted prosthesis, wherein theaction of capturing vibrations entails capturing the vibrations at alocation in a space formed between a middle ear of the recipient and thelocation of occluding.
 47. A method of evaluating an implantedprosthesis, comprising: operating the implanted prosthesis; capturingvibrations generated by a transducer of the prosthesis during saidoperation; comparing the captured vibration to a vibration model,wherein the vibrations travel from the transducer, through therecipient, to a vibration capture apparatus that captures thevibrations; and evaluating the performance of the implanted prosthesisbased on the comparison; wherein: the prosthesis is a hearingprosthesis; the captured vibrations are captured sound; and thevibration model is a sound model; wherein: the action of operating theimplanted prosthesis entails providing the implanted prosthesis with astimulus signal that does not include an acoustic signal in the form ofsound traveling through air to a microphone of the prosthesis.
 48. Thesystem of claim 35, wherein: the vibration module is a model based onthe ideal output from the hearing prosthesis for a given vibratingcomponent stimulation.